Bone compression device

ABSTRACT

The invention relates to bone compression devices and bone compression systems, and in particular, to bone compression devices and systems for use in connection with vertebrae. The bone compression devices and bone compression systems are disposed, or installed, along at least one bone to maintain the at least one bone in a desired spatial relationship. Broadly, the invention is directed to a bone compression device for placing in communication with at least one bone having a bone radius of curvature, the bone compression device comprising a plate having a pre-formed shape, a deformed shape, and at least one elastic shape therebetween, the pre-formed shape having a pre-formed radius of curvature less than the bone radius of curvature, the deformed shape having a deformed radius of curvature greater than the bone radius of curvature, and at least one of the at least one elastic shapes having an elastic radius of curvature that substantially corresponds to the bone radius of curvature. The invention is also directed to a bone compression system wherein the plate includes a string attached to each end of the plate and a tensioner for facilitating the movement of the plate from the pre-formed shape to the at least one elastic shape. Methods of maintaining a bone in a spatial relationship and methods of contouring the bone compression devices are also disclosed.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of co-pending U.S. patent applicationSer. No. 12/241,512, filed Sep. 30, 2008, which is a continuation ofU.S. patent application Ser. No. 11/428,693, filed Jul. 5, 2006, nowabandoned, which is a division of U.S. patent application Ser. No.10/273,853, filed Oct. 17, 2002, now U.S. Pat. No. 7,115,129, whichclaims the benefit of U.S. Provisional Patent Application Ser. No.60/344,980, filed Oct. 19, 2001. Each of these prior applications areincorporated by reference herein in their entirety.

BACKGROUND OF THE INVENTION

1. Field of the Invention

This invention relates to surgical devices, and in particular, to bonecompression devices for maintaining bones, namely, one or morevertebrae, in a desired spatial relationship. The invention also relatesto methods for maintaining at least one bone in a spatial relationshipand methods for contouring the bone compression devices for use inmaintaining bones in a desired spatial relationship.

2. Description of Related Art

The use of bone compression devices in connection with vertebrae areknown in the art. Many of these prior bone compression devices aredirected to fusing together two or more vertebrae. However, the successrate of fusing together four or more levels is extremely low, i.e.,approximately 50% as compared to approximately 95% for two level fusionand 98%-99% for single level fusion. At least one reason contemplatedfor the increase in the percentage of failures of the bone compressiondevices is that the hone compression devices do not substantiallycorrespond to the anatomical curvature of the bone to which they areapplied. Accordingly, prior to installation, or implantation by thesurgeon, the bone compression devices must be. manipulated or shaped tosubstantially correspond to the shape of the bone or bones. As thelength of the bone compression device increases, e.g., to fuse three ormore vertebrae, the amount of manipulation, e.g., bending, requiredgenerally increases. As a result of this manipulation, the bonecompression device may become permanently deformed, and thus weakened,or experience hysteresis.

As with most all materials used to form surgical implants and devices,e.g., titanium and stainless steel and various alloys, the devicesinclude a pre-formed shape, i.e., the shape of the device as formedduring manufacture, and a deformed shape, i.e., the shape of the deviceafter sufficient force is exerted on the device to permanently changethe shape of the device. In between the pre-formed shape and thedeformed shape are numerous elastic shapes. These elastic shapes have atendency to revert back toward the pre formed shape over a period timeranging from near immediacy, e.g., a few seconds, to a number of weeksor even months. In fact, most materials experience a certain amount ofreversion of shape immediately and then, over an extended period oftime, experience additional amounts of reversion of shape. Thisreversion of shape is referred to as hysteresis. One example ofhysteresis is illustrated in materials having what has been referred toas “metal memory.” Because of hysteresis, many prior bone compressiondevices do not remain properly shaped and ultimately fail.

Both the weakening of the bone compression device and hysteresis isfurther complicated by the use of fasteners, e.g., bone screws or bolts,to secure the bone compression devise to the bone. If the fastener holesare misshapen during the manipulation by the surgeon, the fasteners,when installed, generally force the bone compression device back to itsoriginal shape, i.e., away from manipulated shape formed by the surgeonto correspond to the shape of the bone.

For example, in one prior approach, the bone compression device isgenerally straight. Because the spine is lordotic, the bone compressiondevice must be manipulated, or bent, by the surgeon to attempt to shapethe bone compression device to correspond to the curvature of the spine.These devices, after implantation, experience hysteresis resulting inthe bone compression device attempting to revert back to its pre-formedshape, i.e., straight. As a result, the bone compression deviceexperiences a higher incidence of failure over long lengths. Suchhysteresis is increased by the installation of the fasteners intomisshapen fastener holes to secure the bone compression device to thebone. As bone screws or other fasteners are inserted to secure the bonecompression device to the bone, pressure is placed on the plate to pushit onto the bone resulting in the plate straightening out, i.e., beingmanipulated away from the shape desired by the surgeon.

In another prior approach, the bone compression device is slightlycontoured to approximate the curvature of the bone to which the bonecompression device is to be connected. However, the pre-formed curvatureof the bone compression device rarely, if ever, accurately correspondsto the curvature of the bone to which it is to be implanted. Therefore,the surgeon must still manipulate these bone compression devices toprovide additional lordosis or curvature to correspond to the curvatureof the bone. While the amount of manipulation by the surgeon may belessened, these bone compression devices also experience hysteresisresulting in potential failure of the bone compression device.

Accordingly, prior to the development of the present invention, therehas been no bone compression device or bone compression system forplacing in communication with at least one bone having a bone radius ofcurvature, methods of maintaining at least two vertebrae in a spatialrelationship with each other, or methods of contouring bone compressiondevices, which: decrease the rate of failure of the bone compressiondevices due to hysteresis; utilize hysteresis to increase the rate ofsuccess of the bone compression devices; decrease the rate of failure ofthe bone compression devices when employed on long bones or multiplebones, e.g., three or more vertebrae; and provide compressive forces tothe bone to which the bone compression devices are implanted, therebyincreasing the grip of the bone compression device on the bone.Therefore, the art has sought bone compression devices and bonecompression systems for placing in communication with at least one bonehaving a bone radius of curvature, methods of maintaining at least twovertebrae in a spatial relationship with each other, and methods ofcontouring bone compression devices, which: decrease the rate of failureof the bone compression devices due to hysteresis; utilize hysteresis toincrease the rate of success of the bone compression devices; decreasethe rate of failure of the bone compression devices when employed onlong bones or multiple bones, e.g., three or more vertebrae; and providecompressive forces to the bone to which the bone compression devices areimplanted, thereby increasing the grip of the bone compression device onthe bone. It is believed that the present invention will achieve theseobjectives and overcome the disadvantages of other compression devicesand bone compression systems for placing in communication with at leastone bone having a bone radius of curvature, methods of maintaining atleast two vertebrae in a spatial relationship with each other, andmethods of contouring bone compression devices in the field of theinvention, but its results or effects are still dependent upon the skilland training of the operators and surgeons.

SUMMARY OF INVENTION

In accordance with the present disclosure, there is provided a method ofperforming surgery including providing a bone compression deviceincluding a fastener and a surgical plate having a first portionconfigured to be attached to a first vertebral body and a second portionconfigured to be attached to a second vertebral body, wherein thesurgical plate is transitionable between a first state in which thesurgical plate has a pre-formed shape and a second state in which thesurgical plate has a deformed shape. The method further includestransitioning the surgical plate from the first state to the secondstate, disposing the surgical plate on the first and second vertebralbodies, securing the surgical plate to the first and second vertebralbodies with the fastener; and releasing the surgical plate to apply biasto the first and second vertebral bodies.

In another embodiment, the method may further include placing a bonegraft between the first and second vertebral bodies prior to disposingthe surgical plate on the first and second vertebral bodies.

In still another embodiment, the pre-formed shape may have a radius ofcurvature less than that of the deformed shape.

In still yet another embodiment, transitioning the surgical plate fromthe first state to the second state may include applying straighteningforces to each of the first and second portions of the surgical plate.In addition, transitioning the surgical plate from the first state tothe second state may further include contouring the surgical plate tocorrespond to a bone radius of curvature defined by the first and secondvertebral bodies by applying straightening forces to the surgical plate.Furthermore, transitioning the surgical plate from the first state tothe second state may also include applying straightening forces to thesurgical plate such that the surgical plate has a radius of curvaturegreater than that of the first and second vertebral bodies.

In still yet another embodiment, the bone compression device may definefirst and second holes adjacent the first and second portions of thesurgical plate, respectively.

In still yet another embodiment, securing the surgical plate to thefirst and second vertebral bodies may include placing a fastener througheach of the first and second holes defined adjacent the first and secondportions of the surgical plate, respectively.

In still yet another embodiment, the bone compression device may furtherinclude first and second attachment members disposed adjacent the firstand second portions of the surgical plate, respectively.

In accordance with another embodiment of the present disclosure, thereis provided a method of maintaining at least two vertebral bodies in aspatial relationship with each other. The method includes providing abone compression device including a fastener, a surgical plate having afirst portion configured to be attached to a first vertebral body and asecond portion configured to be attached to a second vertebral body, anda tensioner including a shaft and a string coupled to the first andsecond portions of the surgical plate, wherein the surgical plate istransitionable between a first state in which the surgical plate has apre-formed shape and a second state in which the surgical plate has adeformed shape, and the tensioner is configured to transition thesurgical plate from the first state to the second state. The methodfurther includes actuating the tensioner to transition the surgicalplate from the first state to the second state, disposing the surgicalplate on the first and second vertebral bodies, securing the surgicalplate to the first and second vertebral bodies with the fastener; andreleasing the surgical plate to apply bias to the first and secondvertebral bodies.

In another embodiment, actuating the tensioner may include rotating theshaft in a first direction.

In still another embodiment, releasing the surgical plate may includerotating the shaft in a direction opposite the first direction.

In still another embodiment, disposing the surgical plate on the firstand second vertebral bodies may include maintaining tension in thestring.

In still yet another embodiment, the method may further include placinga bone graft between the first and second vertebral bodies prior todisposing the surgical plate on the first and second vertebral bodies.

In still yet another embodiment, the pre-formed shape may have a radiusof curvature less than that of the deformed shape.

In still yet another embodiment, disposing the surgical plate on thefirst and second vertebral bodies may include applying pressure on thesurgical plate against the first and second vertebral bodies.

In still yet another embodiment, releasing the surgical plate to applybias to the first and second vertebral bodies may include removing thepressure applied on the surgical plate against the first and secondvertebral bodies.

BRIEF DESCRIPTION OF DRAWINGS

FIG. 1A is a longitudinal side view of a human spinal column.

FIG. 1B is a detailed side view of two human vertebrae having a diskdisposed between the two vertebrae.

FIG. 1C is a detailed side view of two human vertebrae with a bone graftdisposed between two vertebrae.

FIG. 2 is a schematic showing the radius of curvature of a longitudinalcurve.

FIG. 3A is a longitudinal side view of a prior art bone compressiondevice before being formed into its implantation shape.

FIG. 3B is a longitudinal side view of the prior art bone compressiondevice shown in FIG. 3 a in its implantation shape.

FIG. 4 is a longitudinal side view of a specific embodiment of the bonecompression device of the present invention.

FIG. 5 is a top view of the bone compression device shown in FIG. 4.

FIG. 6 is a longitudinal side view of another specific embodiment of thebone compression device of the present invention.

FIG. 7 is a top view of the bone compression device shown in FIG. 6.

FIG. 8 is a side view of a specific embodiment of the tensioner of onespecific embodiment of the bone compression system of the presentinvention.

FIG. 9 is a side view of a specific embodiment of the string of onespecific embodiment of the bone compression system of the presentinvention.

FIG. 10 is side view of one specific embodiment of the bone compressionsystem of the present invention.

While the invention will be described in connection with the preferredembodiment, it will be understood that it is not intended to limit theinvention to that embodiment. On the contrary, it is intended to coverall alternatives, modifications, and equivalents, as maybe includedwithin the spirit and scope of the invention as defined by the appendedclaims.

DETAILED DESCRIPTION AND SPECIFIC EMBODIMENTS

The present invention is directed to bone compression devices and bonecompression systems for maintaining at least one bone in a desiredspatial relationship. While the description of the bone compressiondevices, bone compression systems, and methods of contouring the bonecompression devices will be directed to use in connection with two ormore vertebrae, it is to be understood that the bone compressiondevices, bone compression systems, methods of maintaining at least twovertebrae in a spatial relationship with each other, and methods ofcontouring the bone compression devices of the invention may be used, orperformed, in connection with any bone in which it is desired tomaintain, or place, at least one bone in a desired spatial relationship,e.g., the pelvis, the femur, the fibula, the tibia, humerus, ulna,radius, or any other bone. For example, the bone compression devices ofthe invention maybe employed in long bone, e.g., femur, and pelvicfracture fixation. Further, the bone compression device may be used inconnection with rigid locked screw-plates and screw-plates that permitsome screw subsidence or angulation, both of which are bone compressiondevices known in the art.

In the preferred embodiments, the bone compression devices are utilizedto maintain one or more vertebrae, and more preferably, three or morevertebrae, of the spine, and in particular, the cervical vertebrae ofhumans, in a desired spatial relationship. In these embodiments, priorto the installation of the bone compression device, one or more bonegrafts are generally disposed between two or more vertebrae. Asillustrated in FIGS. 1B and 1C, for example, after a disk 26, locatedbetween two vertebrae 21, is removed from spine 20, a bone graft 28,e.g., a portion of the patients' own bone, an allograft (portion of bonedonated from another individual), or synthetic bone grafts or cages orboxes such as those made from carbon fiber, metal (particularlytitanium), or ceramics, is usually disposed in the space created by theremoval of the disk 26. Thereafter, the bone compression devices of theinvention are installed and secured to at least the vertebra 21 disposedabove the graft and the vertebra 21 disposed below the graft.Accordingly, bone graft 28 is compressed between the two vertebrae 21 tomaintain bone graft 28 in a spatial relationship with vertebrae 21.

It is contemplated that the bone compression devices of the inventionare suitable for fusing, e.g., being secured to, more than threevertebrae having one or more grafts disposed between two or more of thevertebrae. Therefore, in these embodiments, the vertebrae in proximityto the removed disk(s) are maintained in a desired spatial relationshipto one another. Therefore, the vertebrae are permitted to heal, and, insome cases, the synthetic bone graft is permitted to be incorporatedinto the vertebrae using bone growth factors and other biologicallyactive substances to facilitate the growth of bone over the syntheticbone graft.

Referring now to FIG. 1 a, spine 20 includes vertebrae 21 and hasposterior side 23 and anterior side 24. Spine 20 includes numerous boneradius of curvatures 22 along the longitudinal length of spine 20. Asshown in FIG. 1A, bone radius of curvatures 22 are identified alonganterior side 24 of spine 20. Although the bone compression devices ofthe invention may be installed, or implanted, along the posterior side23 of spine 20, generally, bone compression devices are implanted alonganterior side 24 of spine 20.

Radius of curvature, as used herein referring to the shape of thebone(s) as well as the shape of the bone compression devices andsystems, is measured by determining the radius of a circle formed by thelongitudinal curve of the bone (bone radius of curvature) or bonecompression device (pre-formed radius of curvature, deformed radius ofcurvature, and elastic radius of curvature) placed along thecircumference of the circle formed by the longitudinal curve of the boneor bone compression device. Accordingly, the larger the circle formed bythe longitudinal curve of the bone or bone compression device, thelarger the corresponding curvature, i.e., the greater the radius ofcurvature. Therefore, as the longitudinal curve approaches a straightline, the radius of curvature approaches infinity. FIG. 2 illustrateshow radius of curvature R is determined along curvature L with respectto circle A having center C.

As illustrated in FIGS. 3A and 3B, one prior bone compression device 10includes plate 11 having longitudinal length 13. As shown in FIG. 3A,plate is generally straight. As such, it must be manipulated, e.g.,bent, to correspond to the shape of the bone to which it will beimplanted. In other words, bone compression device 10 must bemanipulated to correspond to the bone radius of curvature. As shown inFIG. 3B, plate 10 is bent in the direction of arrows 12 and 14 to createthe desired radius of curvature. However, due to hysteresis, after plate11 is bent in this manner plate 11 begins to revert back to its originalshape (FIG. 3 a) by moving in the direction of arrows 16 and 18.Alternatively, plate 11 is bent to its deformed shape, thereby weakeningplate 11.

Referring now to FIGS. 4-7, in one aspect the present invention isdirected to bone compression device 40 having plate 50, first end 51,second end 52, upper surface 53, lower surface 54, longitudinal axis 55along length L of plate 50, and lateral axis 56 along width W of plate50. Length L and Width W may have any measurement desired or necessaryto secure bone compression device 40 the bone(s) desired to becompressed. For example, in embodiments in which three or more vertebraeare desired to be compressed, Length L must be of a distance sufficientto permit attachment of bone compression device 40 to each vertebrae.Therefore, length L of plate 50 will be greater in embodiments in whichfive vertebrae are to be compressed as compared to embodiments in whichonly two vertebrae are to be compressed.

Plate 50 also includes at least one fastener hole 58 for receivingfastener (not shown), e.g., bone screws, bolts, etc., to facilitatesecuring plate 50 to the bone. Preferably, each fastener hole is angledsuch that each fastener is placed through fastener holes 58 to besecured into the bone at an angle, thereby facilitating securing plate50 to the bone. Additionally, multiple fastener holes 58 are disposedalong the length L and width W of plate 50 as desired or necessary tofacilitate securing plate 50 to the bone. For example, in embodiments inwhich three or more vertebrae are to be secured by bone compressiondevice 40, plate 50 will preferably include fastener holes 58 such thatat least one fastener will be inserted and secured to each of thevertebrae. Therefore, the total number of fastener holes 58 will bedependent upon the size of plate 50, the number of bones to becompressed, and the size of the bone(s) to be compressed.

Generally, plate 50 includes at least one fastener hole 58 disposed nearfirst end 51 and at least one fastener hole 58 near second end 52. Asshown in FIGS. 4-7, plate 50 preferably includes at least two fastenerholes 58 near first end 51 and two fastener holes 58 near second end 52.An advantage of this embodiment is that fasteners, e.g., bone screws,may be place through fastener holes 58 and secured into the bone, andthus securing plate 50 to the bone, in a manner that lessens thetorsional resistance of plate 50. For example, a first fastener may beused to secure plate 50 to the bone by placing and securing the fastenerthrough the upper right fastener hole 58 in FIG. 5. Next, a secondfastener may be used to secure plate 50 to the bone by placing andsecuring the fastener through the lower left fastener hole 58 in FIG. 5.A third fastener may then be used to secure plate 50 to the bone byplacing and securing the fastener through the upper left fastener hole 58 in FIG. 5. Thereafter, a fourth fastener may be used to secure plate 50 to the bone by placing and securing the fastener through the lowerright fastener hole 58 in FIG. 5. All four fasteners may then betightened as necessary to secure plate 50 to the bone.

Preferably, plate 50 includes plate interface, e.g., plate interfacehole 57, for receiving a tool, e.g., tensioner 70 discussed in greaterdetail below, to facilitate handling of plate 50, moving plate 50 fromits pre-formed shape to at least one of its at least one elastic shapes,and placement of plate 50 along the bone.

Pre-formed radius of curvature, deformed radius of curvature, and eachof the at least one elastic radius of curvature therebetween aredetermined based upon the curvature of plate 50 along longitudinal axis55 or lateral axis 56. As shown in FIGS. 4 and 6, plate 50 is in itspre-formed shape having pre-formed radius of curvature defined by thelongitudinal curvature of lower surface 54.

Plate 50 preferably includes at least two attachment members 59. In theembodiment shown in FIGS. 4-5, each attachment member 59 is hole 61. Inthe embodiment shown in FIGS. 6-7, each attachment member 59 is loop 62.

While it is to be understood that the material from which bonecompression device 50 is formed maybe any material known to persons ofordinary skill in the art, the preferred material is titanium or othermaterial having a relatively low coefficient of elasticity, therebyreducing the total number of elastic shapes bone compression device maytake. As is readily apparent to those skilled in the art, the number ofelastic shapes the bone compression device may take will depend on thematerial from which bone compression device is formed. Materials havinga high coefficient of elasticity will have many more elastic shapes thana material having a low coefficient of elasticity. Suitable materialsinclude titanium, titanium-vanadium-aluminum,cobalt-chromium-molybdenum, as well as any other alloy, metal, or othermaterial approved by the Food and Drug Administration.

Additionally, plate 50 may have any two or three dimensional shape,size, or thickness desired or necessary to be sufficiently secured toone or more bones.

As discussed above, plate 50 preferably includes at least two attachmentmembers, e.g., hole 61 or loop 62, for facilitating the contouring ofplate 50, for example, by string 80 (FIG. 9) and tensioner 70. As shownin FIG. 8, tensioner 70 includes shaft 71 and spool 72. Spool 72preferably includes a ratchet (not shown) to further facilitate windingstring 80 around spool 72 and applying straightening forces to plate 50.Tensioner 70 also preferably includes at least one plate interfacemember 73 having interface member end 74 for interfacing with plate 50,e.g., by inserting at least one plate interface member 73 into at leastone corresponding plate interface hole 57 disposed along plate 50, tofurther secure plate 50 to tensioner 70 thereby facilitating placementof plate 50 along the bone as well as tightening string 80 around spool72. Interface member end 74 preferably is shaped to correspond with theshape of the plate interface. In one embodiment, plate interface hole 57is a fastener hole 58. Tensioner 70 may also include handle 75 tofacilitate gripping and turning tensioner 70 while tightening string 80around spool 72.

As illustrated in FIG. 9, string 80 includes first end 81 and second end82 and may be releasably secured to plate 50 through any manner known topersons skilled in the art. For example, string 80 may be passed througheach attachment member 59 and tied in a knot 86 (FIG. 10). Therefore,after installation of plate 50, each knot may be cut to release plate50. Alternatively, as shown in FIG. 8, first end 81 and second end 82 ofstring 80 may include hook 64 to be passed through each attachmentmember 59 to secure plate 50 during installation. Thereafter, each hook64 may be removed from each attachment member 59 thereby releasing plate50.

String 80 maybe formed out of any material known to persons skilled inthe art provided that string 80 is strong enough to withstand thetensioning forces applied to string 80 during use without breaking.Preferred materials for forming string 80 include Kevlar and otherpolymers having high tensile strength.

Referring now to FIG. 10, tensioner 70 is placed in contact with plate50 by inserting plate interface member 73 into plate interface hole 57.First end 81 of string 80 is passed through attachment member 59, i.e.,hole 61 in FIG. 10, and tied into knot 86 to secure first end 81 toplate 50. Likewise, second end 82 of string 80 is passed throughattachment member 59, i.e., hole 61 in FIG. 10, and tied into knot 86 tosecure second end 82 to plate. String 80 is then wrapped around spool 72of tensioner 70. Tensioner 70 may then be turned in the direction ofarrow 90 to wind, or wrap, string 80 around spool 72. In doing so,string 80 exerts forces on plate 50 whereby place 50 is manipulated, ormoved, in the direction of arrows 91 and 92 (straightening forces) to atleast one of the elastic shapes of plate 50 until the elastic radius ofcurvature substantially corresponds to the bone radius of curvature,i.e., the implantation shape. Plate 50 may then be installed along oneor more bones. After placement of plate 50 along one or more bones,tensioner 70 is turned in the opposite direction of arrow 90. Therefore,due to hysteresis, plate 50 will have a tendency to move in the oppositedirection of arrows 91 and 92. In doing so, plate 50 will be furthersecured to the bone or bones.

In another aspect, the present invention is directed to methods ofmaintaining a bone in a spatial relationship, and in particular, atleast two vertebrae in a spatial relationship with each other utilizingthe bone compression devices discussed above. With respect to use of thebone compression devices for maintaining two or more vertebrae isspatial relationship with each other, first, bone compression device 40is contoured by moving bone compression device 40 from its preformedshape to at least one of the at least one elastic shapes correspondingto the bone radius of curvature. The bone radius of curvature is formedby the at least two vertebrae. Bone compression device 40 is thendisposed along the bone radius of curvature and secured to the at leasttwo vertebrae.

This method of maintaining at least two vertebrae in a spatialrelationship with each other may be used in connection with theinsertion of at least one bone graft between the at least two vertebraeprior to securing the bone compression device to the at least twovertebrae. Accordingly, the bone compression devices facilitatemaintaining the bone graft between the vertebrae as well as maintainingthe at least two vertebrae in a spatial relationship with each other.

It is also noted that the bone compression devices may also be used formaintaining at least three, at least four, and at least five vertebraein a spatial relationship with each other. Another feature of the methodof maintaining at least two vertebrae in a spatial relationship witheach other.

The methods of maintaining at least two vertebrae in a spatialrelationship with each other may also include steps directed to order inwhich the fasteners are inserted through the fastener holes 58. Forexample, in one embodiment, bone compression device 40 includes fourfastener holes 58 (FIGS. 4-7). The first fastener hole 58,101 near firstend 51 (upper left in FIGS. 5 and 7) is disposed diagonally from fourthfastener hole 58,104 near second end 52 (lower right in FIGS. 5 and 7)and second fastener hole 58,102 near first end 51 (upper right in FIGS.5 and 7) is disposed diagonally from third fastener hole 58,103 nearsecond end 52 (lower left in FIGS. 5 and 7). A first fastener is theninserted through first fastener hole 58,101 and first end 51 of plate 50is secured to the bone (one of the at least one vertebrae). A secondfastener is then inserted through fourth fastener hole 58,104 and secondend 52 of plate 50 is secured to the bone (one of the at least onevertebrae). First end 51 of plate 50 is then further secured to the bone(one of the at least two vertebrae) with a third fastener insertedthrough second fastener hole 58, 102, and second end 52 of plate 50 isfurther secured to the bone (one of the at least two vertebrae) with afourth fastener inserted through the third fastener hole 58,103. It isbelieved that by inserting the fasteners through the fastener holes 58to secure plate 50 to the bone in this manner, torsional resistance islessened, thereby increasing the likelihood that bone compression device40 will not be loosened over time.

It is to be understood that the invention is not limited to the exactdetails of construction, operation, exact materials, or embodimentsshown and described, as obvious modifications and equivalents will beapparent to one skilled in the art. For example, while the bonecompression device illustrated and described above, is discussed inconnection with vertebrae, it may be used to with any other individualbone or bones. The dimensions and shapes, as well as the means forattaching the bone compression device to any bone, or number of bones,can be easily determined by a person of ordinary skill in the art.Moreover, while the bone compression devices have been described asbeing installed on the anterior side of the spine or other bone, thebone compression devices may be installed on the posterior side of thespine or other bone. Additionally, the bone compression devices may beinstalled on any vertebrae, i.e., lumbar, thoracic, cervical, or sacral.Further, the lower surface of the plate may include projections, orspikes, to facilitate securing the plate to the bone. Moreover, theplate interface member and corresponding plate interface may be anyshape desired or necessary to permit the plate interface to securelycapture the plate interface and thus permit manipulation and placementof the plate during installation of the plate. Additionally, the bonecompression device may lack a distinguishable longitudinal axis, e.g.,have a squared shape, or have the pre-formed, deformed, and elasticradii of curvature disposed along the width or lateral axis instead ofthe length or longitudinal axis. Accordingly, the invention is thereforeto be limited only by the scope of the appended claims.

1. A method of performing surgery comprising: providing a bonecompression device including: a surgical plate having a first portionconfigured to be attached to a first vertebral body and a second portionconfigured to be attached to a second vertebral body, the surgical platetransitionable between a first state in which the surgical plate has apre-formed shape and a second state in which the surgical plate has adeformed shape; and a fastener; transitioning the surgical plate fromthe first state to the second state; disposing the surgical plate on thefirst and second vertebral bodies; securing the surgical plate to thefirst and second vertebral bodies with the fastener; and releasing thesurgical plate to apply bias to the first and second vertebral bodies.2. The method according to claim 1, further comprising placing a bonegraft between the first and second vertebral bodies prior to disposingthe surgical plate on the first and second vertebral bodies.
 3. Themethod according to claim 1, wherein the pre-formed shape has a radiusof curvature less than that of the deformed shape.
 4. The methodaccording to claim 1, wherein transitioning the surgical plate from thefirst state to the second state includes applying straightening forcesto each of the first and second portions of the surgical plate.
 5. Themethod according to claim 1, wherein transitioning the surgical platefrom the first state to the second state further includes contouring thesurgical plate to correspond to a bone radius of curvature defined bythe first and second vertebral bodies by applying straightening forcesto the surgical plate.
 6. The method according to claim 1, whereintransitioning the surgical plate from the first state to the secondstate includes applying straightening forces to the surgical plate suchthat the surgical plate has a radius of curvature greater than that ofthe first and second vertebral bodies.
 7. The method according to claim1, wherein the bone compression device defines first and second holesadjacent the first and second portions of the surgical plate,respectively.
 8. The method according to claim 7, wherein securing thesurgical plate to the first and second vertebral bodies includes placinga fastener through each of the first and second holes defined adjacentthe first and second portions of the surgical plate, respectively. 9.The method according to claim 1, wherein the bone compression devicefurther includes first and second attachment members disposed adjacentthe first and second portions of the surgical plate, respectively.
 10. Amethod of maintaining at least two vertebral bodies in a spatialrelationship with each other, the method comprising: providing a bonecompression device including: a surgical plate having a first portionconfigured to be attached to a first vertebral body and a second portionconfigured to be attached to a second vertebral body, the surgical platetransitionable between a first state in which the surgical plate has apre-formed shape and a second state in which the surgical plate has adeformed shape; a fastener; and a tensioner including a shaft and astring coupled to the first and second portions of the surgical plate,the tensioner configured to transition the surgical plate from the firststate to the second state; actuating the tensioner to transition thesurgical plate from the first state to the second state; disposing thesurgical plate on the first and second vertebral bodies; securing thesurgical plate to the first and second vertebral bodies with thefastener; and releasing the surgical plate to apply bias to the firstand second vertebral bodies.
 11. The method according to claim 10,wherein actuating the tensioner includes rotating the shaft in a firstdirection.
 12. The method according to claim 11, wherein releasing thesurgical plate includes rotating the shaft in a direction opposite thefirst direction.
 13. The method according to claim 10, wherein disposingthe surgical plate on the first and second vertebral bodies includesmaintaining tension in the string.
 14. The method according to claim 10,further comprising placing a bone graft between the first and secondvertebral bodies prior to disposing the surgical plate on the first andsecond vertebral bodies.
 15. The method according to claim 10, whereinthe pre-formed shape has a radius of curvature less than that of thedeformed shape.
 16. The method according to claim 10, wherein disposingthe surgical plate on the first and second vertebral bodies includesapplying pressure on the surgical plate against the first and secondvertebral bodies.
 17. The method according to claim 16, whereinreleasing the surgical plate to apply bias to the first and secondvertebral bodies includes removing the pressure applied on the surgicalplate against the first and second vertebral bodies.